Control of arterial smooth muscle tone

ABSTRACT

An apparatus for locally controlling smooth muscle tone includes a first electrode for insertion into an artery; a barrier for preventing the first electrode from contacting an arterial wall; a second electrode; a power supply; and a controller for coupling the power supply to the electrodes. The controller is configured to cause the electrode to maintain a waveform for controlling polarization of smooth muscle tone.

CLAIM OF PRIORITY

This application is a continuation of and claims the benefit of priorityunder 35 U.S.C. § 120 to Hastings et al., U.S. patent application Ser.No. 11/381,238, entitled “Control of Arterial Smooth Muscle Tone,” filedon May 2, 2006, which is hereby incorporated by reference herein in itsentirety.

FIELD OF DISCLOSURE

This disclosure relates to medical devices, and in particular, todevices for controlling smooth muscle tone.

BACKGROUND

The arteries and arterioles (collectively referred to as “arterial bloodvessels”) throughout the body are lined with smooth muscle. This smoothmuscle regulates the flow of arterial blood. Relaxation of the smoothmuscle dilates the arterial blood vessel, permitting free flow of blood.Contraction of the smooth muscle constricts the arterial blood vessel,thereby constricting the flow of blood.

Relaxation and contraction of smooth muscle also have an effect on bloodpressure. Relaxation increases the volume of the arterial blood vessel,thereby reducing blood pressure. Such blood vessels are said to be“vasodilated.” Contraction reduces the volume of the arterial bloodvessel, thereby increasing blood pressure. Such blood vessels are saidto be “vasoconstricted.”

When a person suffers a heart attack, a tendency exists for bloodpressure to fall. In an effort to counteract this tendency, theautonomic nervous system causes smooth muscles throughout much of thevascular system to contract. The resulting system-wide vasoconstrictionraises blood pressure.

Among the vasoconstricted arterial blood vessels are the renal arteryand its associated renal arterioles. Constriction of these arterialblood vessels hampers the kidneys' ability to remove excess fluid. As aresult, blood volume increases beyond normal levels. The heart, which isalready in weakened condition, encounters difficulty pumping thisquantity of blood. As a result, this excess blood can accumulate in theheart and cause the heart to pump less efficiently. In addition, theexcess fluid can be excreted into the lungs, resulting in pulmonarycongestion, which in turn may cause difficulty breathing.

It is possible to provide drugs that reduce blood pressure. But thesedrugs act systemically and therefore counteract what is, for most partsof the arterial system, an effective response to the drop in bloodpressure caused by heart failure.

It is also known that smooth muscle tone may be locally controlled bycontacting the arterial wall with an electrode and providing a suitableelectrical stimulation. However, this requires that the arterial bloodvessel be large enough to permit insertion of an electrode. As a result,it is difficult to use this method to control smooth muscle tone in thearterioles. Moreover, there are often a great many arterioles that willneed to be vasodilated. A procedure that relies on contacting the wallof each such arteriole would thus be impractical.

SUMMARY OF INVENTION

The invention is based on the recognition that because the blood iselectrically conductive, one can effectively broadcast instructions tosmooth muscle tissue lining the arterial blood vessels by using theblood vessels themselves as a communication channel. This is achieved byidentifying the location of one or more targeted blood vessels andplacing a pair of electrodes in such a way that the path of leastresistance for current flowing between the two electrodes includes thetargeted blood vessel(s).

In one aspect, the invention features an apparatus for locallycontrolling smooth muscle tone. The apparatus includes a first electrodefor insertion into an artery; a barrier for preventing the firstelectrode from contacting an arterial wall; a second electrode; a powersupply; and a controller for coupling the power supply to theelectrodes. The controller is configured to cause the electrode tomaintain a waveform for controlling polarization of smooth muscle tone.

Embodiments include those in which the first electrode includes a stent,and those in which the first electrode includes a distal tip of acatheter.

Other embodiments include those in which the second electrode includesconducting pads for placement on the skin of a patient, and those inwhich the second electrode includes a distal tip of a catheter.

Additional embodiments include those in which the barrier includes astent defining a lumen for receiving the first electrode, those in whichthe barrier includes a housing surrounding the first electrode, those inwhich the barrier includes a cage surrounding the first electrode, andthose in which the barrier includes a pair of bumpers disposed on eitherside of the electrode.

Among the various embodiments are those in which the controller isconfigured to generate a waveform having pulses of alternating polarity,those in which the controller is configured to generate a waveformhaving pulses of a single polarity, and those in which controller isconfigured to generate a waveform that is synchronized with the cardiaccycle.

Certain other embodiments include a sensor for providing data indicativeof the cardiac cycle to the controller, and/or a local sensor forproviding data indicative of blood pressure local to the firstelectrode.

In another aspect, the invention features a method for regulating smoothmuscle tone within an arterial bed of a patient by inserting a firstelectrode into an artery of the patient; providing a second electrode ata location selected such that current from the first electrode to thesecond electrode traverses the arterial bed; and generating a voltagewaveform between the first and second electrode. The voltage waveform isselected to control polarization of smooth muscle tissue within thearterial bed.

In some practices of the invention, providing a second electrodeincludes providing a surface electrode for placement on the patient'sskin In other practices, providing a second electrode includes insertinga second electrode into a patient's vein.

Some practices of the invention also include selecting the artery to bea renal artery, and/or selecting the location of the second electrode tobe skin adjacent to the kidney.

A variety of waveforms can be generated. In some practices, generating avoltage waveform includes generating a waveform having an excitationcycle and a cleaning cycle. In others, generating a waveform includesgenerating an excitation cycle that overlaps the diastole portion of thepatient's cardiac cycle.

Additional practices of the invention include synchronizing the waveformwith the patient's cardiac cycle.

Additional practices include selecting the arterial bed to be anarterial bed that serves a tumor, and/or selecting the arterial bed toinclude arteries feeding a hemorrhage and/or selecting the arterial bedto include the penile arteries.

Yet other practices of the invention include obtaining a measurementindicative of systemic hypertension, and generating the voltage waveformin response to the measurement.

Other practices of the invention include generating a positive voltageduring the excitation cycle, and generating a negative voltage duringthe excitation cycle.

Other features and advantages of the invention will be apparent from thefollowing detailed description, the claims, and the accompanyingfigures, in which:

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1, 12, and 13 show stimulation systems;

FIG. 2 shows a balloon enclosing the electrode from the stimulationsystems of FIG. 1, 12, or 13;

FIGS. 3 and 4 are longitudinal and transverse cross-sections of theballoon of FIG. 2;

FIG. 5 shows an electrode surrounded by a cage;

FIG. 6 shows an electrode surrounded by a housing;

FIG. 7 shows an electrode protected by a pair of bumpers;

FIG. 8 shows a non-linear electrode;

FIG. 9 shows an electrode placed within a lumen defined by a stent;

FIG. 10 shows a stimulation system that uses a pair of stents aselectrodes;

FIG. 11 shows an excitation waveform for use in the stimulation systemsof FIGS. 1, 12 and 13;

FIG. 12 shows a stimulation system that uses a stent as a barrier; and

FIG. 14 shows a catheter inserted into a blood vessel.

DETAILED DESCRIPTION

Local control of smooth muscle tone in an arterial bed is achieved bycausing electric current to flow through the arterial bed. The resultingcurrent is sufficient in amplitude to locally control the polarizationof smooth muscles throughout the arterial bed. Depending on the polarityof the current, smooth muscles can be locally depolarized orhyperpolarized.

One embodiment, shown in FIG. 1, is intended to locally dilate arterialblood vessels that serve the renal system. This embodiment includes acatheter 9 having a first electrode 10 at its distal tip. The catheter 9is inserted through a femoral artery 12 and maneuvered until the firstelectrode 10 reaches a proximal renal artery 14. A second electrode 16is then placed on the skin 18 adjacent to the kidney 20.

The first and second electrodes 10, 16 are then connected to respectivepositive and negative terminals of a power supply 22. However, in otherapplications, in which one seeks to promote vasoconstriction rather thanvasodilation, this polarity is reversed. The first and second electrodes10, 16 are thus monopolar electrodes. However, bipolar or multipolarelectrodes can also be used since there is no requirement that allterminals of an electrode be connected to a power supply 22.

In some embodiments, the first electrode 10 is a bare portion of anotherwise electrically insulated guide wire. However, in such cases,there remains a possibility of contact between the first electrode 10and the arterial wall. Such contact would result in some current flowinginto the arterial wall instead of remaining in the bloodstream to reacharterioles downstream from the first electrode 10.

FIG. 1 thus shows one representative embodiment of a catheter 9 havingone or more electrodes 10 for placement within a blood vessel that feedsa targeted arterial bed. Current from the catheter-borne electrodes 10flows through the arterial bed on its way to a return electrode padplaced on the patient's skin over the region supplied by the targetedarterial bed. To achieve vasodilation, the catheter-born electrode 10 isoperated as an anode, and the return electrode pad 10 is operated as acathode. To achieve vasoconstriction, the return electrode pad 10 isoperated as an anode, and the catheter-borne electrode 10 is operated asa cathode. The catheter-borne electrode 10 and the return electrode pad16 are configured so that the electric field lines, and thereforecurrent flow, traverse the target arterial bed.

In other embodiments a barrier surrounds the first electrode 10. Asuitable barrier, shown in FIG. 2, is a balloon 24 such as those used ina balloon catheter. This balloon 24 prevents the first electrode 10 fromactually contacting the arterial wall.

FIG. 3 shows a longitudinal cross-section of a balloon catheter 26 withthe balloon 24 fully deployed. In the configuration shown, the balloon24 functions as a barrier to prevent direct contact between theelectrode 10 and the wall of the artery 14. The electrode 10 supports anelectric field, which in turn provides an electromotive force sufficientto propel current through the bloodstream between the first and secondelectrodes 10, 16.

FIG. 4 shows a transverse cross-section of the balloon catheter 26 inFIG. 2. The balloon 24, in its deployed state, has a generally circularcross-section, the radius of which varies along the length thereof, withminima at proximal and distal ends of the balloon 24.

The balloon 24 is inflated with a fluid, which can be gas or liquid, andeither electrically insulating or conductive. The pressure of this fluidis selected to provide sufficient turgidity to prevent the electrode 10from contacting the balloon 24, but enough flexibility to avoidimpairing a surgeon's ability to maneuver the catheter 26 through thevascular system.

The balloon 24 is typically made of a biocompatible material, such aslatex or silicone. The interior of the balloon 20 is in fluidcommunication with a pump (not shown) that selectively inflates ordeflates the balloon. For this purpose, a flexible tube 28 typicallyextends along the catheter 26 between the pump and the interior of theballoon 20.

While a balloon 24 as described above will tend to act as a barrier tolow-frequency current, at higher frequencies, there may be capacitativecoupling between the electrode 10 and the balloon 24. This, in turn, maycause sufficient charge to be on the surface of the balloon 24, in whichcase contact between the balloon 24 and the arterial wall may result insome current within the wall itself.

Another example of a barrier is a mesh or net cage 30 such as that shownin FIG. 5. The cage 30 can be rigid, or slightly flexible, but withenough resistance to cushion the electrode 10 against accidentallycontacting the cage 30. The cage 30 can be made of either an insulating,or a conductive material. However, if the cage 30 is made of aconductive material, it is best electrically isolated from the electrode10, so that the potential at the electrode 10 need not match thepotential of the cage 30.

The overall shape of the cage 30 is similar to that of the balloon 24shown in FIGS. 2-4. This shape, which is generally ellipsoidal orovaloid, provides a low profile while reducing the likelihood of traumashould the cage contact the arterial wall.

Yet another example of a barrier, shown in FIG. 6, is a housing 32 thatencloses the electrode 10. The housing can completely enclose theelectrode 10, or it can have holes 34, as shown in FIG. 6, through whichblood can enter and exit the housing 32, thereby providing directelectrical contact between the electrode and the blood. The housing 32likewise has an ellipsoidal or ovaloid shape to provide both a lowprofile and to avoid trauma should the housing inadvertently contact thearterial wall.

Another embodiment, shown in FIG. 7, includes a barrier in the form of apair of bumpers 35 a, 35 b disposed proximal and distal to the firstelectrode 10. In this embodiment, the electrode 10 contacts the blooddirectly, while the bumpers 35 a, 35 b prevent the electrode 10 fromcontacting the arterial wall.

In the embodiments described thus far, the electrode 10 has been astraight length of wire. However, suitable electrodes can assume anynumber of shapes. For example an electrode 60 might be helical, as shownin FIG. 8. Such an electrode provides greater surface area forelectrical contact, while remaining compact enough to be readilymaneuvered.

Electrodes that have a non-linear shape, such as that shown in FIG. 8,can be configured to retract into a sheath. Such retraction enables asurgeon to more easily maneuver the distal tip of the catheter to itsdestination. In such cases, there exists a mechanism to cause theelectrode 10 to assume its desired shape when extended outside of thesheath.

One such mechanism includes an electrode guide-wire made of ashape-memory alloy to which the electrode 10 is mechanically coupled. Insuch a case, the shape-memory alloy is configured to have, as itsremembered shape, the desired shape of the electrode 10. When theelectrode guide-wire and the electrode 10 are retracted into the sheath,both are fully extended. When the electrode guide-wire, is extended outof the sheath, it assumes its remembered shape, thereby causing theelectrode, to which it is mechanically coupled, to likewise assume thatshape. Alternatively, the electrode 10 can itself be made of ashape-memory alloy, in which case no electrode guide-wire is necessary.

The first electrode 10 can also be prevented from touching the arterialwall by first implanting an insulated stent 36 in the region in whichelectrical activation is planned, as shown in FIG. 9. Then, the firstelectrode 10 is inserted through the artery 14 until it reaches thestent 36. Since the stent 36 is made of an insulating material, itfunctions as a barrier to current.

FIG. 10 shows a longitudinal cross-section of another embodiment inwhich a stent 38 includes an insulating layer 40 on which is placed acylindrical first electrode 10. A cylindrical second electrode 16 can beplaced on an additional stent 42 having a similar insulation layer andplaced in another blood vessel 46 elsewhere in the vascular system. Animplanted power supply 22 provides a voltage difference between the twoelectrodes 10, 16. Stent-mounted electrodes of this type are disclosedin copending U.S. application Ser. No. 10/951,213 filed on Sep. 27,2004, the contents of which are herein incorporated by reference.

FIG. 9 is representative of a more general configuration in which afirst electrode 10 is implanted in an artery feeding a targeted arterialbed, and a second electrode 16 is implanted in a vein draining thetargeted arterial bed. The power supply 22, which is typically an energystorage element or battery, together with any control electronics, ismounted near either one of the implanted electrodes 10, 16 and connectedto the other implanted electrode 16, 10 with a conductive, insulatedwire. Alternatively, the power supply 22 and any control electronics areimplanted in a third location and connected to the implanted electrodes10, 16 by conductive, insulated wires. The power supply 22 can berecharged by an external source of energy, such as an RF transmitter.Alternatively, the power supply 22 can be recharged by an implantedbioelectric generator that transforms body motion or body heat intoelectrical energy. In some cases, the implanted electrodes 10, 16 arepowered entirely from an external power supply 22 such as an RFtransmitter. The implanted control electronics may be programmed fromoutside the body.

As shown in FIG. 1, the second electrode 16 can be a surface electrode,such as a conductive pad placed on the skin A second electrode 16 placedon the skin is particularly useful for treatment of acute episodes ofunwanted vasoconstriction. For treatment of chronic vasoconstriction,the second electrode 16 can be placed in a convenient vein, as suggestedby FIG. 10, or in tissue. The relative placement of the first and secondelectrodes 10, 16 is selected such that the path of least electricalresistance between the two electrodes 10, 16 includes the arterial bloodvessels that are to be dilated.

Once the power supply 22 is turned on, a controller 48, shown in FIG. 1,modulates the flow of electric current from the first electrode 10 tothe second electrode 16. On its way, the electric current passes throughthe renal artery 14, and through the remainder of the arterial bloodvessels serving the renal system. This electric current flows pastsmooth muscle cells lining the renal artery 14 and arterioles. Thepresence of positive charge is believed to hyperpolarize these smoothmuscle cells, thereby causing them to relax. This, in turn, would beexpected to dilate the arterial blood vessels serving the renal system.As a result, the kidneys 20 would be able to remove excess fluid fromthe blood even as the remainder of the vascular system remainsvasoconstricted.

In the configuration shown in FIG. 1, the polarity of the electric fieldis such as to hyperpolarize the endothelial cells. Since a change in themembrane potential of the endothelial cells is transmitted across gapjunctions to the underlying smooth muscle cells, it is possible toinhibit contraction of the smooth muscle by hyperpolarizing theendothelium alone.

FIG. 11 shows a typical voltage waveform provided to the first electrode10. The controller 48 causes the power supply 22 to maintain a largepositive voltage during diastole and a small negative voltage at allother times. The optional negative voltage is particularly useful toreduce fouling of the electrode 10. In some practices, the duration ofthe negative voltage is chosen so that the charge delivered during thenegative portion of the waveform balances the charge delivered duringthe positive portion of the waveform. Suitable voltages are those thatcause an electric field of 50 to 2000 volts/meter. Given theconductivity of blood, this translates to current densities of on theorder of 25-1000 amperes/meter². However, some embodiments maintainvoltages of 100 to 1000 volts/meter, which translates into currentdensities of 50-500 amperes/meter².

In some practices, at least one property of the voltage waveform issynchronized with heart rate. Synchronization can be achieved usinglocally measured blood flow, blood pressure, or an ECG(electro-cardiogram) signal.

The positive voltage is typically applied during a period of low bloodflow, which in peripheral arteries occurs primarily during diastole. Theapplication of a positive voltage during diastole is believed to behelpful because the higher fluid velocity associated with systole tendsto sweep the larger particles in the blood into the center of theartery. Since most of these particles are negatively charged, the higherfluid velocity already leaves the arterial wall naturally hyperpolarizedduring systole. In contrast, during diastole, with its slower fluid flowvelocity, the negatively charged particles tend to congregate on thewall, thereby tending to neutralize the positive charge on the wall.Thus, it is during diastole that inducing positive charges is mosthelpful for maintaining hyperpolarization.

The waveform of FIG. 11 can be varied. For example, in someimplementations, there is no negative voltage. Instead, the electrode 10is made neutral. In other implementations, the positive pulse is reducedin amplitude and/or extended in duration. In other implementations, thepulses and the cardiac cycle are asynchronous.

In some applications, the polarity of the electrodes is reversed. Insuch cases, the stimulation is like that shown in FIG. 11, but withpolarities reversed. When polarity is reversed, stimulation is typicallyperformed during systole instead of diastole.

The electrical stimulation can also be delivered in a waveform that maycontain shaped features and/or pulses having both positive and negativepolarity components at one or more frequencies. The electricalstimulation need not be constant. There may be time intervals duringwhich the stimulation is turned off.

In an alternative embodiment, shown in FIG. 12, the controller 26 is afeedback controller coupled to a sensor 50. The sensor 24 is configuredto detect an indicator of the cardiac cycle and to provide cardiac cycledata to the controller 48. Suitable indicators of cardiac cycle includeheart beat, blood pressure, flow velocity, or any physical quantity fromwhich the current state of the cardiac cycle can be derived. Thecontroller 48 uses this cardiac cycle data to adaptively vary theinterval between the positive pulses shown in FIG. 10. Typical pulsewidths range between half the cardiac cycle and 40 milliseconds.

In another embodiment, shown in FIG. 13, the controller 48 receivesfeedback from a local sensor 52 that measures a property at the targetsite itself. For example, current flowing in the vicinity of theelectrode 10 may have a tendency to heat the surrounding blood. To avoidexcessive heating, the local sensor 52 can be a temperature sensormounted at the distal tip of the catheter. The temperature sensorprovides a temperature signal to the controller 48. In response to thetemperature signal, the controller 48 regulates the voltage waveform soas to avoid excessive local heating.

Other local characteristics can also be measured by the local sensor 52.For example, the local sensor 52 can be a pressure sensor that providesa pressure signal on the basis of which the controller 48 determineswhether a desired local blood pressure has been achieved.

A typical catheter 9 shown in FIG. 14, features a flexible tube 54having a distal end 56 connected to a distal tip assembly 58 and aproximal end 60 coupled to a handle 62. Within the distal tip assembly58 are the first electrode 10 and any of the ancillary structuresdescribed above. Extending through the tube 54 is a guide-wire 64, adistal end of which, in some embodiments, also functions as the firstelectrode 10. A proximal end of the guide-wire 64 is coupled to thehandle 62. A trigger 66 mounted on the handle 62 enables a surgeon toselectively connect the power supply 22 to the first and secondelectrodes 10, 16. Both the catheter 9 and its distal tip assembly 58are sized and shaped to pass through a cannula 68 inserted into a bloodvessel, which in FIG. 14 is the femoral artery 12.

Additional applications of the foregoing configurations include dilatinga coronary artery bed distal to an occlusion in patients suffering fromacute myocardial infarction. Such dilation may hasten re-perfusion andprevent micro-embolic occlusion of arterioles distal to the occlusion,thereby minimizing loss of myocardium. Dilation of the arterial beddistal to an ischemic stroke may offer the same benefits to affectedbrain parenchyma. Dilation of vascular beds supplying the lung, forexample by an electrode implanted into the pulmonary artery, is usefulfor treatment of primary pulmonary hypertension. On-demand dilation ofpenile arteries using a remote-controlled implanted stimulator may helpresolve male sexual dysfunction. Systemic hypertension may be controlledby dilation of selected peripheral arterial beds. In this application,implanted electrodes may stimulate dilation in response to an implantedblood pressure sensor, or via remote programming of implanted controlcircuitry.

In other applications, electrical stimulation can be applied toautonomic nerves to treat a variety of disorders. In such applications,the first and second electrodes 10, 16 are placed near damaged tissueenervated by autonomic nerves. The electrodes 10, 16 are brought nearthe region either by passing them through a blood vessel that servesthat damaged tissue, or by direct insertion into the damaged tissue.Electrical stimulation can be applied to sympathetic or parasympatheticefferent nerves to stimulate or relax tissues respectively, or toafferent nerves to demand attention from the brain or to block signalssuch as pain from reaching the brain.

For example the apparatus of the present invention can be used to blockpain signals originating in nociceptive nerves. When connected to theterminals of the power supply 22, the electrodes 10, 16 cause current toflow into the tissue. This current hyperpolarizes the nociceptivenerves, thereby preventing them from depolarizing. Since the nociceptivenerves provide the sensation of pain to the brain, thishyperpolarization brings about a cessation, or significant diminution,of pain. In addition, current delivered through arterial blood vesselsfeeding the injured tissue dilates those blood vessels. As a result,more blood is available to nourish the injured tissue, thereby promotingits healing.

The foregoing method of increasing blood supply to nourish selectedtissue can be reversed in cases in which one wishes to retard blood flowto, or growth of, selected tissue. Reversal of polarity negativelycharges the blood vessel wall, thereby reducing the magnitude of themembrane potential, and potentially causing vasoconstriction. It isadditionally possible to induce local constriction at the site of thestimulating electrode by stimulating the sympathetic nerve thatconstricts the smooth muscle. By selectively constricting arteries, onecan reduce flow of arterial blood to selected tissues, therebyinhibiting growth of, and perhaps causing ischemic death of thosetissues. This is particularly useful when the selected tissue is, forexample, a cancerous tumor, particularly, one that has yet tometastasize. Yet another application of selective vasoconstriction isthat of inducing vasoconstriction to reduce blood flow to one or morearteries feeding the site of hemorrhage. This is particularly useful fortreating a hemorrhagic stroke.

An apparatus as described herein can be used to deliver a variety oftherapies in the acute hospitalization setting. Such therapies include,but are not limited to: selective dilation of one or both renal arterialbeds to increase urine output and reduce blood volume; dilation of anarterial bed distal to a blockage in a coronary, cerebral or otherartery to provide increased blood flow to ischemic tissue followingremoval of the offending stenosis, and to allow flushing and passage ofmicro-emboli through small blood vessels distal to the blockage; andvasoconstriction of arteries feeding the site of a hemorrhagic stroke.

Implanted electrodes as described herein can also be used to delivertherapy chronically or periodically. Such therapies include, but are notlimited to: vasodilation of selected peripheral arterial beds to treatsystemic hypertension; vasodilation of selected arterial beds to treatlocal hypertension, for example primary pulmonary hypertension;vasodilation of the penile arteries to treat male sexual dysfunction;and vasoconstriction of an arterial bed feeding a tumor to treat cancer.

1. An apparatus for locally inhibiting smooth muscle tone to causedilation of arterioles within an arterial bed, the apparatus comprising:a first electrode and a second electrode, wherein the first and secondelectrodes are configured to be inserted into an artery that feeds thearterial bed, wherein the artery and arterial bed includes arterialtissue and the arterial tissue includes smooth muscle tissue and anendothelium; a power supply; and an electronic controller configured tocouple the power supply to the electrodes, wherein the controller isconfigured to use the electrodes to induce and maintain positive chargeswithin the artery feeding the arterial bed to induce and maintainhyperpolarization of the endothelium, locally inhibiting smooth musclecontraction to cause dilation of arterioles within the arterial bed. 2.The apparatus of claim 1, further comprising: a sensor coupled to thecontroller, wherein the sensor is configured to provide data indicativeof the cardiac cycle to the controller, wherein the controller isconfigured to use the cardiac cycle in response to induce positivecharges within the artery during ventricular diastole.
 3. The apparatusof claim 1, further comprising a stent configured to function as thefirst electrode or the second electrode.
 4. The apparatus of claim 1,wherein the first electrode or the second electrode is a distal tipelectrode of a catheter.
 5. The apparatus of claim 1, wherein thecontroller is configured to generate a waveform having pulses ofalternating polarity.
 6. The apparatus of claim 1, wherein thecontroller is configured to generate a waveform having pulses of asingle polarity.
 7. The apparatus of claim 1, wherein the sensor is alocal sensor configured to provide data indicative of blood pressurelocal to the first electrode and the second electrode within the artery.8. The apparatus of claim 1, wherein the first electrode and the secondelectrode are configured to be inserted into a femoral artery that feedsan arterial bed within a renal system.
 9. An apparatus for locallyinhibiting smooth muscle tone to cause dilation of arterioles within anarterial bed, the apparatus comprising: a first electrode and a secondelectrode, wherein the first and second electrodes are configured to beinserted into an artery that feeds the arterial bed, wherein the firstelectrode is a distal tip electrode, and wherein the artery and arterialbed includes arterial tissue and the arterial tissue includes smoothmuscle tissue and an endothelium; a blood pressure sensor configured tosense blood pressure in the artery; a power supply; and an electroniccontroller configured to receive sensed blood pressure from the bloodpressure sensor and to couple the power supply to the electrodes,wherein the controller is configured to use the sensed blood pressureand the electrodes to induce and maintain positive charges within theartery feeding the arterial bed to induce and maintain hyperpolarizationof the endothelium, locally inhibiting smooth muscle contraction tocause dilation of arterioles within the arterial bed.
 10. The apparatusof claim 9, wherein the controller is configured to generate a waveformsynchronized with a cardiac cycle.
 11. The apparatus of claim 10,wherein the waveform has pulses of alternating polarity.
 12. Theapparatus of claim 10, wherein the waveform has pulses of a singlepolarity.
 13. The apparatus of claim 10, wherein the waveform has anexcitation cycle that overlaps a diastole portion of the cardiac cycle.14. The apparatus of claim 10, wherein the waveform has a positivevoltage synchronized to a diastole portion of the cardiac cycle.
 15. Theapparatus of claim 10, wherein the first electrode and the secondelectrode are configured to be inserted into a femoral artery that feedsan arterial bed within a renal system.
 16. A method, comprising:inserting a first electrode and a second electrode into an artery thatfeeds an arterial bed of arterioles, wherein the artery and arterial bedincludes arterial tissue and the arterial tissue includes smooth muscletissue and an endothelium; and hyperpolarizing the endothelium, whereinhyperpolarizing the endothelium includes using the first electrode andthe second electrode within the artery to induce and maintain positivecharges within the artery feeding the arterial bed, wherein inducing andmaintaining hyperpolarization locally inhibits smooth muscle contractionto cause dilation of arterioles within the arterial bed.
 17. The methodof claim 16, wherein inserting includes inserting the first electrodeand the second electrode into a femoral artery.
 18. The method of claim17, wherein the arteriole bed is within a renal system.
 19. The methodof claim 16, wherein inserting includes inserting a tip electrode. 20.The method of claim 16, wherein inserting includes inserting a stentelectrode.
 21. The method of claim 16, wherein using the first electrodeand the second electrode within the artery to induce and maintainpositive charges within the artery includes generating a stimulationwaveform to be delivered using the first electrode and the secondelectrode, wherein generating the stimulation waveform includesgenerating the waveform with a single polarity.
 22. The method of claim16, wherein using the first electrode and the second electrode withinthe artery to induce and maintain positive charges within the arteryincludes generating a stimulation waveform to be delivered using thefirst electrode and the second electrode, wherein generating thestimulation waveform includes generating the waveform with alternatingpolarity.
 23. The method of claim 16, further comprising: sensing bloodpressure in the artery, wherein using the first electrode and the secondelectrode within the artery to induce and maintain positive chargeswithin the artery includes generating a stimulation waveform and usingthe sensed blood pressure to control generation of the stimulationwaveform.
 24. The method of claim 16, further comprising: sensing acardiac cycle, wherein using the first electrode and the secondelectrode within the artery to induce and maintain positive chargeswithin the artery includes generating a stimulation waveformsynchronized to the cardiac cycle.